Apparatus, System, and Method for Selective Stimulation

ABSTRACT

An implantable neurostimulator system is disclosed, the neurostimulator system comprising a hollow cylindrical electronics enclosure having a top, a bottom, and a side; a coil extending from a first part of the electronics enclosure; and at least one electrode operatively connected to the electronics enclosure.

STATEMENT OF RELATED APPLICATIONS

This application is related to International Patent Application No.[Docket No. 069737-5004-WO], and claims the benefit of U.S. PatentApplication Nos. 60/978,519 and 61/017,614 and 61/136,102, filed on Oct.9, 2007 and Dec. 29, 2007 and Aug. 12, 2008 respectively, which areincorporated herein by reference in their entirety.

FIELD OF THE INVENTION

The present invention relates to an apparatus, system, and method forimplantable therapeutic treatment of a patient.

BACKGROUND OF THE INVENTION

Acute and chronic conditions such as pain, arthritis, sleep apnea,seizure, incontinence, and migraine are physiological conditionsaffecting millions of people worldwide. For example, sleep apnea isdescribed as an iterated failure to respire properly during sleep. Thoseaffected by sleep apnea stop breathing during sleep numerous timesduring the night. There are two types of sleep apnea, generallydescribed in medical literature as central and obstructive sleep apnea.Central sleep apnea is a failure of the nervous system to produce propersignals for excitation of the muscles involved with respiration.Obstructive sleep apnea (OSA) is caused by physical obstruction of theupper airway channel (UAW).

Current treatment options range from drug intervention, non-invasiveapproaches, to more invasive surgical procedures. In many of theseinstances, patient acceptance and therapy compliance is well belowdesired levels, rendering the current solutions ineffective as along-term solution.

Implants are a promising alternative to these forms of treatment. Forexample, pharyngeal dilation via hypoglossal nerve (XII) stimulation hasbeen shown to be an effective treatment method for OSA. The nerves arestimulated using an implanted electrode. In particular, the medial XIInerve branch (i.e., in. genioglossus), has demonstrated significantreductions in UAW airflow resistance (i.e., increased pharyngealcaliber).

Implants have been used to treat other conditions as well. For example,stimulation of the vagus nerve is thought to affect some areas in thebrain prone to seizure activity; sacral nerve stimulation is anFDA-approved electronic stimulation therapy for reducing urgeincontinence; and stimulation of peripheral nerves may help treatarthritis pain.

While electrical stimulation of nerves has been experimentally shown toremove or ameliorate certain conditions (e.g., obstructions in the UAW),current implementation methods typically require accurate detection of acondition (e.g., a muscular obstruction of an airway), selectivestimulation of a muscle or nerve, and a coupling of the detection andstimulation components. Additionally, attempts at selective stimulationhave focused on activating entire nerves or nerve bundles. A needtherefore exists for an apparatus and method for selectively activatingonly the portion of the nerve responsible for activating the desiredmuscle or muscle groups while avoiding activation of unwanted muscles ormuscle groups.

Accordingly, the present invention is directed to an apparatus, system,and method for selective stimulation that substantially obviates one ormore problems due to limitations and disadvantages of the related art.

SUMMARY OF THE INVENTION

The present invention includes an implantable neurostimulator systemwith a hollow cylindrical electronics enclosure having a top, a bottom,and a side; a coil extending from a first part of the electronicsenclosure; and at least one electrode operatively connected to theelectronics enclosure.

In another embodiment, an implantable neurostimulator system includes asymmetrical chevron-shaped molded body having an apex, a first andsecond side, and a base; a coil at the apex of the molded body; anelectronics enclosure at least partially integral with the molded body;and at least one electrode operatively connected to the electronicsenclosure.

In a further embodiment, an implantable neurostimulator system includesan electronics enclosure; a coil; and at least one perforated cuffelectrode operatively connected to the electronics enclosure.

In yet another embodiment, an implantable neurostimulator systemincludes an electronics enclosure; a coil; and at least oneflat-bottomed open trough electrode operatively connected to theelectronics enclosure.

Another embodiment of the invention includes an apparatus and method ofneurostimulation, the method including the steps of at least partiallyencircling a nerve with a cuff having a first and second surface, thecuff having at least one contact on one of the first and secondsurfaces; connecting at least one stimulus generator to the at least onecontact; and delivering a stimulus to the at least one contact.

It is to be understood that both the foregoing general description andthe following detailed description are exemplary and explanatory, andare intended to provide further explanation of the claimed invention.

BRIEF DESCRIPTION OF THE DRAWINGS

The accompanying drawings, which are included to provide a furtherunderstanding of the invention and are incorporated in and constitute apart of this specification, illustrate embodiments of the invention, andtogether with the description serve to explain the principles of theinvention. In the drawings:

FIGS. 1A-1F show an exemplary embodiment of a mastoid bone implantablepulse generator (IPG) implant;

FIGS. 2A-2D show an exemplary embodiment of a sub-mandibular implantablepulse generator (IPG) implant;

FIGS. 3A-3C show exemplary embodiments of IPG cables and connectors;

FIGS. 4A-4D show exemplary embodiments of IPG power systems;

FIGS. 5A-5D show exemplary embodiments of IPG accessories;

FIGS. 6A-6G show exemplary embodiments of IPG electrodes;

FIGS. 7A and 7B show exemplary embodiments of monopole electrodeconfigurations;

FIG. 8 shows an exemplary embodiment of a bipolar electrodeconfiguration;

FIGS. 9A and 9B show exemplary embodiments of multipolar electrodeconfigurations;

FIGS. 10A and 10B show an example of a multiplexed system using forcevectoring; and

FIGS. 11A and 11B show exemplary embodiments of non-multiplexed waveformgenerators.

DETAILED DESCRIPTION OF THE INVENTION

Reference will now be made in detail to the embodiments of the presentinvention, examples of which are illustrated in the accompanyingdrawings. Wherever possible, like reference numbers are used for likeelements.

It is to be understood that both the foregoing general description andthe following detailed description are exemplary and explanatory and areintended to provide further explanation of the invention as claimed.Additional features and advantages of the invention will be set forth inthe description that follows, and in part will be apparent from thedescription, or may be learned by practice of the invention. Theobjectives and other advantages of the invention will be realized andattained by the structure particularly pointed out in the writtendescription and claims hereof as well as the appended drawings.

According to some embodiments, an implantable neurostimulator system ofthe present invention includes an implantable pulse generator system(IPG); and at least one electrode operatively connected to the IPG togenerate accurate, selective nerve stimulation patterns. Exemplarycomponents of various embodiments of the claimed invention are describedhereafter.

I. Implantable Pulse Generator Systems (IPGs)

Implantable pulse generator systems (IPGs) include one or more of (1) animplant (e.g., FIGS. 1A-2D); (2) a power system (e.g., FIGS. 4A-4D); and(3) an IPG accessory (e.g., FIGS. 5A-5D). Examples of each are discussedbelow.

A. Exemplary IPG Implants

FIGS. 1A-2D illustrate exemplary embodiments of IPG implants. Referringto FIGS. 1A-1F, an embodiment of the IPG system includes a mastoid boneimplant 100. Referring to FIGS. 2A-2D, another embodiment of the IPGsystem includes a sub-mandibular implant 200.

2. Mastoid Bone Implant

FIGS. 1A-1F illustrate a mastoid bone implant embodiment of an IPG fortreating obstructive sleep apnea. In the exemplary embodiment shown inFIGS. 1A-1F, the mastoid bone implant 100 is implanted into the mastoid,which is a bony portion of the skull behind the ear. The mastoid bonebed is close to the HGN, and provides a stable well-protected locationfor the mastoid bone implant 100.

FIG. 1A illustrates an exemplary embodiment of a unilateral mastoid boneimplant 100 implantable pulse generator system. This area is a commonlocation for cochlear implants. The mastoid bone implant 100 is placedinto a well that is surgically excavated in the mastoid bone below thesurface of the skull to secure the implant in place. Placing the mastoidbone implant 100 in a well protects the implant, reduces the amount itprotrudes from the skull, and provides a lower device profile.

The embodiment shown can be implanted to stimulate the left, right, orboth HGNs. In a unilateral procedure, the mastoid bone implant 100 istypically located on the same side of the head as the HGN beingstimulated. In a bilateral procedure, a tunnel is formed in thepatient's neck from the mastoid bone implant 100 side to the oppositeside for the second HGN lead and electrode. While only one electrode(discussed later) is shown in FIG. 1A, multiple electrodes may be usedwithout departing from the scope of the invention.

a. Physical Configuration

In the exemplary embodiment shown in FIGS. 1A-1F, the mastoid boneimplant 100 has a hollow cylindrical electronics enclosure 110 (alsoknown as a case or a can) with a top 111, a bottom 113, and a side 112.The case 110 houses the implant electronics and power source. The case110 is typically made of a biocompatible material, and may behermetically sealed. In the embodiment shown, a lip 114 encircles atleast a portion of the side 112 of the enclosure 110, and in certainembodiments has one or more holes to allow a surgeon to anchor themastoid bone implant 100 in place with sutures.

In certain embodiments, silastic and/or silicone rubber (referred togenerically as silastic) covers at least a portion of the electronicsenclosure 110. Other materials known to those skilled in the art may beused without departing from the scope of the invention. In embodimentswith a lip 114, the lip may be used to help secure the silastic to theenclosure 110. In certain embodiments, some or all of the remaining caseexterior not covered with silastic acts as an electrode. The electronicsenclosure 110 in FIGS. 1A-1F is exemplary only, and not limited to whatis shown.

An internal coil 120 extends from a first part of the side 112 of theelectronics enclosure 110. In the exemplary embodiment shown, theinternal coil 120 receives power, and supports bidirectional data andcommand telemetry. The internal coil 120 is encased in silastic, whichmay have an internal Dacron mesh or similar cloth for added tearresistance and durability. Similar materials known to those skilled inthe art can be used without departing from the scope of the invention.

In certain embodiments, an internal magnet 130 helps align the internalcoil 120 with an external coil 511 (FIG. 5B). The internal magnet 130may be hermetically sealed, and in certain embodiments is embedded inthe approximate center of the internal coil 120. In certain embodiments,a second magnet (not shown) is located in the external controller coil511. The internal magnet 130 and external controller magnet (not shown)are oriented so that they are attracted to each other when the externalcontroller coil is near the internal coil 120. The attractive force ofthe two magnets brings the two coils close together, helping to maintainalignment between the coils. Aligning the coils helps optimize power andtelemetry data transfer between the external controller and the mastoidbone implant 100.

The mastoid bone implant 100 may be implanted to stimulate the left,right, or both HGNs. In certain embodiments, the mastoid bone implant100 orientation affects the internal magnet 130 orientation. Therefore,in certain embodiments the internal magnet 130 in the mastoid boneimplant 100 is reversible. In other exemplary embodiments, the internalmagnet 130 is removable, for procedures such as an MRI where thepresence of a strong magnet in the patient might affect the imagesobtained or the forces generated and applied to the implanted internalmagnet 130 by the static magnetic field of the MRI system might beunsafe for the patient. In still other embodiments, the internal magnet130 and/or external controller magnet may be replaced with a materialthat is attracted to a magnet, either to eliminate the magnet on oneside of the pair of devices, or to provide a lower profile to thecorresponding coil assembly.

b. Internal Components

In the embodiment shown in FIGS. 1A-1F, one or more glass-to-metalfeedthrough leads 140 extend through the top of the electronicsenclosure 110. In the exemplary embodiment shown, the leads 140 areencased in silastic or similar material. The location of the feedthroughleads 140 is exemplary only, and not limited to what is shown.Feedthrough leads 140 at the top of the electronics enclosure 110 bringelectrode and antenna connections from the enclosure 110 to the internalelectronics. The feedthrough leads 140 shown are glass-to-metalfeedthrough leads, but other non-conducting material known to thoseskilled in the art can be used in place of or in addition to glass tomake the feedthrough leads 140. Gold or nickel wires connect casefeedthrough pins to internal circuitry inside the enclosure 110.Stainless steel, platinum-iridium, gold or MP35N wires connect externalportions of the feedthrough pins to connector, lead, or antennaconnections external to the enclosure 110.

The electronics design within the case 110 varies, often depending onthe implant power source. For example, referring to FIG. 4A, in anexemplary embodiment of an RF implant (discussed later), the implantuses an external controller and power source. Since the power source andcontroller are external to the implant, the internal electronics arerelatively simple. The implant need not have volume for a battery orultracapacitor, and with the controller external to the implant, controland stimulation functions may be reduced to such a significant extentthat a state-machine design could realistically be utilized. This hasthe added advantage of reducing power consumption and hybrid assemblyreal estate area as well, but has the disadvantage of being a moreinflexible design with future product changes requiring a newapplication-specific integrated circuit (ASIC) state machine design.

Other exemplary embodiments have their own power sources. Theseexemplary embodiments have means to charge and protect the internalpower storage elements, and may have means to monitor these functions.Because of this added complexity, and because of the opportunity forindependent operation without constant external supervision, thearchitecture of the IPG electronics may include a microcontroller alongwith the custom ASIC to generate the stimulus pulses and handle chargingand telemetry functions. This has the added benefit of futurefunctionality improvements along with field upgrade options for existingpatients, as well as increased diagnostic functionality. In still otherembodiments, the IPG electronics may include an acoustic pickup andsound processor to identify snoring. The snoring may be used as atrigger to initiate and/or modify stimulus patterns as the patient movesfrom one stage of sleep to another.

In still other embodiments, the mastoid bone implant 100 has an internalRF interface. In these embodiments, RF may be used to send power and/orcontrol signals to the implant. The internal RF interface operatesaccording to the principle of inductive coupling. The internal RFinterface may also include a passive RFID transponder with a demodulatorand a modulator. In certain embodiments, the RFID-based implant exploitsthe near-field characteristics of short wave carrier frequencies ofapproximately 13.56 MHz. In yet another embodiment, the RFID-basedimplant uses frequencies between 10 and 15 MHz. This carrier frequencymay be further divided into at least one sub-carrier frequency.

The internal RF interface may also have a number of othercharacteristics. For example, the internal RF interface may include oneor more of a transponder, internal antenna, modulator, demodulator,clock, and rectifier. The transponder may be passive or active.Furthermore, the transponder may have further separate channels forpower delivery and data and control, and in some embodiments, thetransponder may employ a secure full-duplex data protocol. The RFinterface may further include an inductive coupler, an RF to DCconverter, and an internal antenna, and the antenna may include amagnetic component. In other embodiments, the internal RF interface cansend and/or receive control logic and/or power.

In some embodiments, the internal RF interface uses a sub-carrierfrequency for communication with an external RF interface that may belocated, for example, in an external controller. The sub-carrierfrequency may be used for communication between the internal andexternal RF interfaces and is obtained by the binary division of theexternal RF interface carrier frequency. The transponder may use thesub-carrier frequency to modulate a signal back to the external RFinterface.

c. Connectors

As shown in FIGS. 1B-1F, one or more multi-contact implant connectors150 extending from a second part of the side 112 of the electronicsenclosure 110 opposite the coil 120 connect electrode lead connectors160 with cables having one or more electrode leads to the mastoid boneimplant 100. The type of connector, number of pins, and the location ofthe connectors are exemplary only, and not limited to what is shown.

In one embodiment, the implant connector 150 is a five to nine positionfemale connector, which mates to corresponding lead pins in theelectrode lead connector 160. These electrode lead connections 160extend from cables having one or more electrode leads that connect withelectrode contact connections for four to eight cathodic contacts and asingle or array of common anodes. This configuration allows stimulationto occur between any two or more independent contacts and/or the case110. The receptacles are made of a biocompatible material such asstainless steel, titanium, or MP35N, and arranged in a staggered row orother configuration to reduce space.

In certain embodiments, molded silicone rubber provides a detent featureto the female implant connector 150, which helps hold the male portionof the electrode lead connector 160 in place. Male portions of theelectrode lead connectors 160 optionally have a taper feature providingstrain relief to the lead to prevent stress fracture failures in thelead wires. If a connector is unused, as, for example, in a unilateralimplant for a single HGN, it is protected with a dummy plug (not shown)to prevent tissue ingrowth and isolate any unused contacts from bodilyfluids.

Certain embodiments include suture holes on the connector areas. Thesuture holes help the surgeon lock the connectors together. If used, thesutures help tighten the connection between the male and femaleconnectors. As a non-limiting example, the surgeon may suture around theshroud around the female and male assembled connection to tighten theconnection between elements. Other methods known to those skilled in theart may be used without departing from the scope of the invention.

2. Sub-Mandibular IPG Implant

FIGS. 2A-2D illustrate an embodiment of a sub-mandibular IPG implant 200for treating obstructive sleep apnea (OSA). In this embodiment, thesub-mandibular implant 200 stimulates the hypoglossal nerve (HGN), aperipheral nerve located below and behind the lower mandible. The HGN istypically 4 to 5 mm in diameter, with a typical epineurium thickness ofless than 1 mm. In the embodiment shown, the sub-mandibular implant 200may be placed within the sub-mandibular space. There is minimal nervemotion in this area during sleep. There, the sub-mandibular implant 200,attached leads 342 (FIGS. 3B-3C) (discussed later), and electrodes(FIGS. 6A-6G) (discussed later) are protected from jaw and neck movementrelative to the tissues adjacent to the implanted elements. This helpssecure the sub-mandibular implant 200 in place and prevent migration anddrooping into the neck region. The sub-mandibular implant 200 isminimally invasive and easily implanted.

a. Physical Configuration

In the exemplary embodiment shown in FIGS. 2A-2D, the sub-mandibularimplant 200 is chevron-shaped, roughly triangular with the base 202 ofthe triangle pulled upwards toward the apex 201 of the triangle, withsmooth corners 203 and a small surface area. The apex 201 and corners203 of the sub-mandibular implant 200 are curved to eliminate sharpcorners that may harm a patient. The chevron shape helps thesub-mandibular implant 200 fit within the sub-mandibular space. One ormore holes 204 along each side of the chevron apex 201 optionally allowa surgeon to anchor the sub-mandibular implant 200 in place withsutures. If used, the sutures connect to the fascia attached to thebottom and inner surfaces of the mandible, to help secure thesub-mandibular implant 200 in place and prevent migration and droopinginto the neck region. Because of its shape, the sub-mandibular implant200 may be implanted to stimulate the left, right, or both HGNs. Thesub-mandibular implant 200 orientation with respect to the target HGN isthe same on either HGN, meaning that the sub-mandibular implant 200cannot be incorrectly implanted with respect to its inside or outsidesurface, enabling efficient power and data transfer in anyconfiguration.

In the embodiment shown, the bulk of the sub-mandibular implant 200 issilastic and/or silicone rubber (generically referred to as silastic)with an internal Dacron mesh or similar cloth to add tear resistance anddurability to the package. These materials are exemplary only, and notlimited to what is shown. Other materials known to those skilled in theart may be used without departing from the scope of the invention.

b. Internal Components

In the embodiment shown in FIGS. 2A-2D, an internal coil 210 lies at theapex 201 of the sub-mandibular implant 200. With the internal coil 210located as shown, it is not sensitive to orientation. It functionsequally well whether implanted on the right or left HGN. The internalcoil 210 receives power, and supports bidirectional data and commandtelemetry. The internal coil 210 shown is made of gold or platinum wire,but may be made from other conductive materials known to those skilledin the art without departing from the scope of the invention.

In certain embodiments, an internal magnet 220 helps align the internalcoil 210 with an external coil 511 (FIG. 5B). The internal magnet 220may be hermetically sealed, and in certain embodiments is embedded inthe approximate center of the internal coil 210. In certain embodiments,a second magnet (not shown) is located in the external controller coil511. The internal 220 and external 520 controller magnets are orientedso that they are attracted to each other when the external controllercoil 511 is near the internal coil 210. The attractive force of the twomagnets brings the two coils close together, helping to maintainalignment between the coils. Aligning the coils helps optimize power andtelemetry data transfer between the external controller and thesub-mandibular implant 200.

As previously discussed, the sub-mandibular implant 200 may be implantedto stimulate the left, right, or both HGNs. In certain embodiments,sub-mandibular implant 200 orientation affects the internal magnet 220orientation. Therefore, in certain embodiments the internal magnet 220in the sub-mandibular implant 200 is reversible. In other exemplaryembodiments, the internal magnet 220 is removable, for procedures suchas an MRI where the presence of a strong magnet in the patient mightaffect the images obtained or the forces generated and applied to theimplanted internal magnet 220 by the static magnetic field of the MRIsystem might be unsafe for the patient. In still other embodiments, theinternal magnet 220 and/or external controller magnet (not shown) may bereplaced with a material that is attracted to a magnet, either toeliminate the magnet on one side of the pair of devices, or to provide alower profile to the corresponding coil assembly.

In one embodiment shown in FIGS. 2A-2D, just below the internal coil210, at the base 202 of the chevron, lies an electronics enclosure (thecase) 230 housing the implant electronics and power source. In theembodiment shown, silastic covers at least a portion of the case 230. Incertain embodiments, at least a portion of the case 230 surface is leftexposed to act as an electrode. The case 230 location is exemplary only,as is the portion of the case 230 covered with silastic, and not limitedto what is shown.

The case 230 is typically made of biocompatible metal, such as a 6-4titanium alloy. A titanium alloy is chosen because of its highresistivity compared to commercially pure (CP) titanium. The higherresistivity helps minimize power losses due to eddy currents resultingfrom exposure to RF fields, such as a charging field. Otherbiocompatible materials may be used without departing from the scope ofthe invention. In certain embodiments, the electronics enclosure 230 ishermetically sealed. The enclosure 230 may be any hermetic enclosureknown to those skilled in the art.

Feedthrough leads 240 in the sides of the electronics enclosure 230bring electrode and antenna connections from the enclosure 230 to theinternal electronics. The feedthrough leads 240 shown are glass-to-metalfeedthrough leads, but other non-conducting material known to thoseskilled in the art can be used in place of or in addition to glass tomake the feedthrough leads 240. Gold or nickel wires connect casefeedthrough pins to internal circuitry inside the enclosure 230.Stainless steel, platinum-iridium, gold or MP35N wires connect externalportions of the feedthrough pins to connector, lead, or antennaconnections external to the enclosure 230. In certain embodiments, suchas the embodiment shown in FIG. 3A (discussed later), at least onepermanently attached electrode lead 341 (FIG. 3A) connects theelectrodes and antenna to the sub-mandibular implant 200. Usingpermanently attached electrode leads 341 rather than connectors 350increases system reliability.

The electronics design within the case 230 varies, often depending onthe implant power source. Examples of how the electronics design varieswith the power source are described in the sections discussing themastoid bone implant 100 (above) and are not repeated here.

c. Connectors

FIGS. 3A-3C show exemplary embodiments of IPG electrode leads 341, 342and multi-contact implant connectors 350. Although shown with asub-mandibular implant 200, they may also be used with a mastoid boneimplant 100. The implant connectors 350 connect electrode leads 341, 342and electrodes to the sub-mandibular implant 200. The electrode leads341, 342 and electrodes connect to the implant connectors 350 with leadwires having polyurethane, silicone rubber, or similar insulatingmaterial, and wiring made from stainless steel, MP35N, titanium, 90/10Pt—Ir, gold, or other material with high conductivity, high fatigueresistance, and good tensile properties. The lead wires have highbiocompatibility and high corrosion resistance in implanted stimulationconditions. In certain exemplary embodiments, the wire material is MP35Ndrawn-filled-tube (DFT) with a silver core. This material has excellentfatigue resistance and high tensile strength, and the silver core lowersits electrical resistance to more desirable levels.

In one embodiment, the implant connector 350 is a five to nine positionfemale connector, which mates to corresponding lead pins in theelectrode lead 341, 342. These electrode leads 341, 342 connect withelectrode contact connections for four to eight cathodic contacts and asingle or array of common anodes. This configuration allows stimulationto occur between any two or more independent contacts and/or the case230. The receptacles are made of a biocompatible material such asstainless steel, titanium, or MP35N, and arranged in a staggered row orother configuration to reduce space. One or more multi-contact implantconnectors 350 on at least one corner of the sub-mandibular implant 200connect electrode leads 341, 342 to the sub-mandibular implant 200.

In the embodiment shown in FIG. 3A, at least one electrode lead 341 andelectrode are permanently attached to the sub-mandibular implant 200 atone of its corners. Another feedthrough lead 240 with a female implantconnector 350 is available for attachment of another electrode lead 342and electrode. The embodiment shown in FIG. 3A is typically used forunilateral implant patients, where a single electrode lead 341 issufficient to achieve the desired clinical results, but would stillallow a second electrode lead 342 and electrode to be added forbilateral applications. In the embodiment shown in FIG. 3C, theelectrode leads 342 shown attach to the sub-mandibular implant 200through implant connectors 350 only.

B. Implant Power Systems

FIGS. 4A-4D illustrate exemplary embodiments of IPG power systems. Eachembodiment illustrates a different power system. The four power systemsare (1) RF-powered and controlled (FIG. 4A), with continuous applicationof RF power for operation of the implanted system; (2) ultra-capacitorpowered (FIG. 4B), with at least one short RF-powered charge period tosupply sufficient power to the implant for operation for one sleepperiod; (3) secondary-battery-powered (FIG. 4C), with occasionalRF-powered charging periods to supply sufficient power to the implantfor operation for at least one sleep period a day for a week or more;and (4) a hybrid combination of ultracapacitor and secondary batterypowered (FIG. 4D). In the absence of sufficient internal energy chargein the latter three embodiments, the system would allow operation tooccur as in the first embodiment, that is, continuous application of RFpower for the operation of the implanted system for the duration of thesleep period.

1. RF-Powered IPG Implant

FIG. 4A shows an exemplary embodiment of an RF-powered IPG implant 400.In the embodiment shown, the RF-powered IPG implant 400 has no internalpower source. It receives power and commands, and exchanges data with anexternal controller via an inductively coupled RF power and data link.The link is a flat coil 401 attached via feedthrough pins to a couplingcircuit 402 inside the IPG electronics enclosure. The coil 401 is ACcoupled using one or more capacitors to prevent DC current leakage,which can damage tissue and cause failures in the hermetically sealedIPG feedthroughs.

The power and data signals are sinusoidal or similar waveforms at one ormore frequencies that minimize energy losses but still support thebandwidth requirements for adequate data transfer rates. In certainembodiments, these signals are in the radio frequency (RF) range. In theembodiment shown, RF power and data are supplied externally with amatching coil, which may be held in position over the IPG coil 401 usinga magnet, a strap, adhesive, or other method known to those skilled inthe art. Limited coil misalignment is allowed and expected, includinglateral displacement, vertical displacement, and out of plane angulardisplacement.

In other embodiments, the implant 400 operates according to theprinciple of RFID inductive coupling. The RF may be used to send powerand/or control signals to the implant. In an embodiment, the implant 400exploits the near-field characteristics of short wave carrierfrequencies of approximately 13.56 MHz. This carrier frequency isfurther divided into at least one sub-carrier frequency. The sub-carrierfrequency is obtained by the binary division of the carrier frequency.In certain embodiments, the implant 400 can use between 10 and 15 MHz.The implant 400 may further have two channels, Channel A and Channel B.Channel A is for power delivery and Channel B is for data and control.

In the embodiment shown in FIG. 4A, the received waveform is internallyrectified and converted into one or more supply voltages within theRF-powered IPG implant 400 by coupling circuitry 402 and at least onecircuit 404 used by the RF-powered IPG implant 400 in regularoperations, including stimulation of the HGN. In certain exemplaryembodiments, the circuit 440 may be an application specific integratedcircuit (ASIC). The RF-powered IPG implant 400 uses its internal coil401 to send a signal to the external devices, sometimes on a differentcarrier frequency, chosen to optimize its signal integrity and datatransfer characteristics without interfering with the inbound signaltransfer process. In certain embodiments, the RF-powered IPG implant 400sends the signal from the internal coil 401 concurrently. The supplyvoltages are filtered and stored internally in capacitors. Thecapacitors are sized to power the RF-powered IPG implant 400 duringtemporary interruptions of the power link, but are not large enough topower the RF-powered IPG implant 400 for an entire sleep session.

2. Ultracapacitor-Powered IPG Implant

FIG. 4B shows an exemplary embodiment of an ultracapacitor-powered IPGimplant 410. In the exemplary embodiment shown, the embodiment has thesame elements described above, along with an ultracapacitor 413 that islarge enough to store sufficient energy for a single sleep session, andreceives power at very high rates with insignificant degradation ofperformance over time. In the ultracapacitor-powered IPG implant 410embodiment, the external controller and associated coil are placed overthe internal coil 411 just long enough to exchange data and charge upthe ultracapacitor 413 power storage element. The rate at which theultracapacitor 413 storage element charges is inversely related to thetime required to bring it to full charge—the higher the charge rate, theshorter the charge time. Once the ultracapacitor 413 storage element issufficiently charged, the patient may remove the external controller andexternal coil and begin a sleep session.

3. Secondary-Battery-Powered IPG Implant

FIG. 4C shows an exemplary embodiment of an IPG implant 420 with asecondary battery 423. The secondary-battery-powered IPG implant 420 issimilar to the passive RF-powered IPG implant 400 (FIG. 4A), but with aninternal battery 423 as a secondary source of power. The secondarybattery 423 is large enough to store sufficient energy for at least asingle sleep session and optimally for many more, and in certainembodiments is sufficient for at least a week of use. In thisembodiment, the secondary-battery-powered IPG implant 420 receives itspower for charging the secondary battery 423, receives commands, andexchanges data with an external controller using an inductively coupledRF power and data link. The external controller and its associated coilare placed over the internal coil 421 long enough to exchange data andcharge up the secondary battery 423.

The rate at which the secondary battery 423 may be charged is typicallylonger than the charge times for ultracapacitor embodiments. Chargerates for secondary batteries such as lithium ion and lithium polymerare typically expressed as a percentage of charge capacity, typicallyfrom C/40 to C/1, where C is the charge capacity of the battery. Forinstance, a 200 milliamp-hour (mA-hr) battery could be charged at 50 mAfor a C/4 rate. There is a trade-off for all battery chemistries inperformance and longevity of the battery depending upon both the chargeand discharge rates, as well as the depth of discharge prior to acharging session. High rates of charge and discharge are known to reducethe longevity of a secondary battery system, as well as deeplydischarging a battery, whereas low rates of charge and discharge, andlimited discharge durations with short periods of charge tend to enhancebattery performance and longevity. This translates to a conveniencefactor for the patient in that to lengthen the time between surgicalreplacement for the IPG occurs the patient must frequently charge theirimplanted system, but if the patient desires to only charge whenabsolutely necessary it is more likely that the IPG will have a shorterimplanted lifetime. These issues must be considered by the patient andthe clinician as to how often and how long the device must be recharged.

4. Hybrid Powered IPG Implant

FIG. 4D shows an exemplary embodiment of hybrid-ultracapacitor andsecondary-battery-powered IPG implant 430. In this embodiment, thehybrid-ultracapacitor and secondary-battery-powered IPG implant 430receives power for charging the internal ultracapacitor 433 and itssecondary battery 434, receives commands, and exchanges data with anexternal controller with an inductively coupled RF power and data link.Charge may be stored in the secondary battery 434, allowing sleepsessions with no external hardware for up to a week at a time (exceptfor initial IPG turn-on and final turn-off). The patient may also chargefor just a few moments to fill the ultracapacitor 433, or use thehybrid-ultracapacitor and secondary-battery-powered IPG implant 430 inonly a fall-back operation of ultracapacitor operation only when theservice life of the secondary battery 434 is exhausted, avoiding theneed for surgical replacement.

Other forms of implanted power sources may also be used withoutdeparting from the scope of this invention, such as harvesters ofkinetic energy, fuel cells, and even atomic sources.

C. Exemplary IPG Accessories

In certain embodiments, the IPG interfaces with other devices. FIGS.5A-5D show exemplary embodiments of IPG accessories. The other devicesmay include, for example: (1) an external controller with an integratedor attached coil (FIGS. 5A and 5B); (2) a charging station to replenishenergy to the external controller (FIG. 5D); and (3) a remote controlthat communicates with the controller (FIG. 5C). In certain embodiments,the remote control also establishes the operating mode for the patientand/or monitors the performance of the implant and controller. Theseembodiments are described below.

1. External Controller

FIG. 5A shows an exemplary embodiment of an external controller 500. Inthis embodiment, the external controller 500 has a rechargeable powersource such as a secondary battery system (lithium ion, etc.),electronics to power and communicate with the IPG, and a telemetryportion that communicates with the remote control. The telemetry portionas shown is a coil, but can be any item used by those skilled in the artto transmit and receive data. In the embodiment shown the coil as shownis integrated with the external controller 500, but can be separate fromthe external controller 500 in other embodiments. In the embodimentshown, the telemetry portion between the external controller 500 and theremote control (FIG. 5C) uses Bluetooth or other wireless communicationstandard. Utilizing such a standard allows commonly availabletechnologies to be utilized for the remote control and additionallyallows communication with a computer programming system. The embodimentshown is exemplary only, and not limited to what is shown. In otherembodiments, the external controller 500 communicates with the remotecontrol or clinician's programmer (such as a computer or otherelectronic device) using a cable having a USB or other connection knownto those skilled in the art. The cable can be in addition to or in placeof the wireless telemetry.

The external controller 500 has user interface functions with anactivity indicator, such as, for example, an LED indicating whether thedevice is operational. The interface may also have another indicatorshowing link and activity with the remote control. The externalcontroller 500 interfaces with a recharging station (FIG. 5D), so thatwhen the patient starts or ends a sleep session the controller 500 maybe easily removed from or returned to the recharging station.

In the exemplary embodiment shown in FIG. 5A, the external controller500 is mounted to a collar or neck strap 501 that allows simple fittingof the external controller 500 about the patient's neck and providesoptimal alignment with the sub-mandibular IPG implant 200 (FIGS. 2A-2D)for proper power and data transfer. The neck and sub-mandibular locationof the external controller 500 and sub-mandibular IPG implant 200 areminimally affected by head and neck movement during sleep, with typicalpatient movement during sleep resulting in only minimal forces appliedto the devices.

FIG. 5B shows another exemplary embodiment of an external controller510. In this exemplary embodiment, the controller 510 is worn behind theear (BTE) and is similar in shape to a speech processor used with acochlear implant. This shape gives the BTE controller 510 a low profile,which helps keep it from being dislodged during sleep. This shape isexemplary only, and not limited to what is shown. The controlleroperatively connects to a coil, which is placed near the mastoid boneimplant 100 (FIGS. 1A-1F) prior to sleeping. The controller coiloptionally has a magnet to help align it with the internal coil 120.

The BTE controller 510 has user interface functions with an activityindicator, such as, for example, a charge indicator LED 512 indicatingwhether the device is operational. The interface may also have anothertelemetry indicator LED 513 showing link and activity with the remotecontrol. The BTE controller 510 interfaces with a recharging station(FIG. 5D), so that when the patient starts or ends a sleep session theBTE controller 510 may be easily removed from or returned to therecharging station.

2. Remote Control

FIG. 5C shows an exemplary embodiment of a remote control 530. In theembodiment shown, the remote control 530 provides the patient with asimple and intuitive interface to the IPG system. The remote control 530allows the patient to start and stop IPG operation, and interrogate theIPG system and external controller 500 (FIG. 5A) for proper function,status of the communication and power link to the IPG, and status ofexternal controller 500 power. With the embodiment of the remote control530 shown, the patient may also choose operating modes for the IPG,including but not limited to standard sleep mode, exercise mode, andalternative operating modes. If enabled by the clinician, the remotecontrol 530 also allows the patient to adjust stimulation levels. Theembodiment is exemplary only, and not limited to what is shown. Forexample, the remote control 530 may communicate with the externalcontroller 500 using a cable having a USB or other connection known tothose skilled in the art. The cable can be in addition to or in place ofthe wireless telemetry.

In certain embodiments, the remote control is incorporated into an AppleiPhone™ 520 or other wireless device. The iPhone™ 520 has an excellentuser interface, Bluetooth telemetry capability, and is supported as adevelopment platform for commercial applications. The iPhone™ 520 alsoallows the patient to transfer data to and from the Internet, enablingsecure communications to the clinician and the manufacturer. Using acommercially available remote control also eliminates the need tomanufacture the remote, simplifying the supply, support, and(potentially) the patient learning curve. Using a commercially availablealternative also provides the opportunity to provide extensive helpresources, such as context sensitive help screens, training videos, andlive help from company and clinician support centers if required by thepatient. In certain embodiments, one or more of the iPhone™ 520commercial functions are disabled, with the iPhone™ 520 only acting as aremote control for the external controller 500/IPG system. The iPhone™520 would enable the patient to operate the implant system and haveaccess to help documents and videos that help the patient use thesystem. In other embodiments, one or more of the iPhone™ 520 commercialfunctions are enabled. Other embodiments of the iPhone™ 520, or otherforms of smart phones may also be used, and may be more readilyavailable in certain markets around the world.

In certain embodiments, the external controller 500 interfaces with acomputer. The interface may be wireless, or by a cable having a USB orother connection known to those skilled in the art. The cable can be inaddition to or in place of the wireless telemetry. The computer may be aWindows™, UNIX™, Linux™ or Macintosh™ based notebook or desktop computerhaving Bluetooth communication capability. Other telemetry known tothose skilled in the art may also be utilized. Using telemetry known tothose skilled in the art facilitates compatibility with industrystandards and systems. Other wireless communication standards may beused without departing from the scope of the invention. The computermaintains a database to store all pertinent patient data, includingstimulation settings, follow-up session changes, etc. The computer mayalso have an application with an intuitive method to test and programthe IPG system so that the clinician can set IPG implant stimulationparameters for some or all of its operating modes.

3. Recharging Station

FIG. 5D shows an exemplary embodiment of a recharging station 540. Inthe embodiment shown, the recharging station 540 is a cradle-like devicepowered by a wall-wort power supply. The external controller 500 (FIG.5A) is placed in its cradle for recharging during non-sleep periods.Recharging may be inductive, relying upon the orientation of theexternal controller 500 within the cradle for inductive coupling to themating coils of the devices. Recharging may also utilize metal contacts541 on the exterior surface of the controller for direct recharging tothe external controller 500, much like that of a standard cordlesstelephone handset. In certain embodiments, the wall-wort power supply isa commercially available recharger.

II. Electrodes

The IPG system delivers stimulation to targeted nerves or nerve fibersusing implanted electrodes. In certain embodiments, the electrodesconsist of biocompatible silicone rubber with a Dacron or similar wovenmaterial to lend tear resistance to the design. The electrode contactsare fabricated with 90 percent platinum and 10 percent iridium (90/10Pt—Ir), known in the industry as highly biocompatible materials withexcellent properties for neural excitation. Other materials known tothose skilled in the art may also be used.

Researchers treating obstructive sleep apnea have discovered that themuscles of interest are activated by HGN nerve fibers lying interior tothe HGN with respect to the outside of the patient (i.e., the dorsalaspect of the HGN). FIGS. 6A-6G (discussed below) show exemplaryembodiments of IPG electrodes that take advantage of this neuralorganization. For example, in certain embodiments one or more electrodecontacts lie preferentially on the inside surface of the cuff or troughon the interior portion. Some embodiments have at least four contacts,others as many as eight, which act as excitatory electrode contacts.Other embodiments have additional contacts located longitudinally distalto the excitatory contacts. In these exemplary embodiments, theadditional contacts have a common electrical connection to the IPG case,or are multiplexed to at least one IPG output. This provides many waysof stimulating the HGN nerves, including contact to case indifferent,contact to array indifferent, contact to contact (bipolar ormultipolar), and any combination of the above. These and other exemplaryelectrode embodiments are discussed below.

A. Electrode Designs

Electrodes can be designed in many different ways. Three possibledesigns include the fully encircling cuff (FIGS. 6A-6D), the helicalcuff (FIG. 6E), and the open trough (FIGS. 6F-6G). Embodiments of eachare discussed below. These embodiments are exemplary only, and notlimited to what is shown.

1. Fully-Encircling Cuff Electrodes

FIGS. 6A-6D show exemplary embodiments of fully encircling cuffelectrodes 600. For example, FIG. 6A shows a non-perforated fullyencircling cuff. Non-perforated fully encircling cuffs must be used withcare, as connective tissue buildup in response to a foreign body cancause an increase of HGN 10 diameter and potential constriction of theHGN 10 after surgery. Some swelling of the HGN 10 is expected due to thesurgical trauma the nerve endures when it is dissected and the electrodeis installed. The swelling and increase in connective material maydamage the nerve, due to the effect of pressure on the blood supply ofthe nerve trunk, and the increased pressure on the nerve axons of thetrunk.

In other embodiments, the implantable neurostimulator system of thepresent invention includes a fully encircling perforated cuff electrode605 (FIGS. 6B-6D). In some embodiments, the perforated cuff electrode605 is from about 4 mm to about 12 mm in diameter. In some embodiments,the perforated cuff electrode 605 is from about 6 mm to about 10 mm indiameter. In yet another embodiment, the perforated cuff electrode 605is about 8 mm in diameter.

Alternatively, the diameter of the perforated cuff electrode 605 isexpandable and increases or decreases in accordance with the diameter ofthe HGN 10. In further embodiments, the perforations 607 and/or theplasticity of the material comprising the perforated cuff electrode 605allows accommodation of the expected change in diameter and swellingresponse and prevents ischemic constriction of the HGN 10. In someembodiments, the perforations 607 are about 2 mm in diameter. Theperforated cuff electrode 605 may also be self-sizing. In someembodiments, the fully encircling perforated cuff electrode does notphysically contact the entire circumference of the HGN 10. In stillother embodiments, the perforated cuff electrode 605 overlaps uponitself, thereby creating an empty space 606 into which a nerve mayexpand without ischemic constriction. In certain expandable cuffembodiments, the electrode diameter is expandable, with ranges extendingfrom a diameter of approximately 2 mm to a diameter of approximately 12mm. Other expansion ranges may be used without departing from the scopeof the invention.

In some embodiments, the perforated cuff electrode 605 includeselectrical contacts 608 on its inner surface facing a nerve. Theperforated cuff electrode 605 may include any number and/or arrangementof contacts 608. For example, the perforated cuff electrode 605 caninclude at least six contacts 608. In other embodiments, the perforatedcuff electrode 605 includes at least eight contacts 608. In certainembodiments, the contacts 608 are axially aligned relative to theperforations 607 of the perforated cuff electrode 605 (FIG. 6B).

Alternatively, the contacts 608 can be axially staggered relative to theperforations 607 (FIGS. 6C-6D). In some embodiments, the contacts 608are about 1 mm in diameter. In still other embodiments, the distancebetween contacts 608 is about 1 mm. The contacts 608 need notcircumscribe the entire circumference of the nerve. In certainembodiments, the flap of the electrode cuff overlaps an electrode lead(FIGS. 6B-6C) and in others it does not (FIG. 6D). In furtherembodiments, the positions of the contacts 608 relative to a nervechanges as the diameter of the nerve increases or decreases. The contactsize, number, location, and arrangement are exemplary only, and notlimited to what is shown. Other combinations may be used withoutdeparting from the scope of the invention.

2. Helical Cuff Electrodes

FIG. 6E shows an exemplary embodiment of a helical cuff electrode 610.The helical cuff electrode 610 mitigates the problems of a fullyencircling cuff electrode 600 (FIG. 6A). One example is a helical cuffelectrode developed by the Huntington Medical Research Institute forstimulating the vagus nerve. In this example, the cuff electrode 610winds around a nerve trunk, but does not overlap itself and is notsutured into a fixed diameter. In still other exemplary embodiments, thecuff electrode 610 is self-sizing. A self-sizing cuff encircles thenerve in its natural state. The cuff electrode 610 overlaps its ends butstill allows some expansion of the cuff until the connective tissueovergrowth assumes its final state after surgical implantation.

3. Open Trough Electrodes

FIG. 6F shows an exemplary embodiment of a round-bottomed open troughelectrode 620. In the exemplary embodiment shown, the contacts 621reside on the inside of the trough. In certain round-bottomed opentrough embodiments, contacts 621 are present on the innermost region ofthe interior of the trough, while the portion of the trough that coversthe outer portion of the HGN 10 has no contacts.

The open trough electrode 620 addresses some of the problems associatedwith the fully encircling electrode 600 design by lying underneath thenerve trunk, rather than completely encircling or enclosing the nervetrunk. This allows tissue expansion and swelling, as well as theconnective tissue buildup, while still allowing the nerve to expand awayfrom the trough without constriction. The exemplary open troughelectrode 620 embodiment shown slips underneath the HGN 10 with littledissection. The normal forces holding the tissues of the neck in placehelp keep the HGN 10 aligned with the open trough electrode 620. Theopen trough electrode 620 may optionally be anchored to surroundingtissue to maintain its position with respect to the HGN 10 to preventdistension or other loading forces upon the HGN 10.

In some embodiments of the present invention, it is desirable to placethe contacts 621 of an open trough electrode 620 preferentially againstone surface of the nerve bundle, and it is also desirable to avoidplacing any forces against the nerve as it lies in the electrode 620 toforce it into a new or different shape from its native shape. In someembodiments, the open trough electrode 620 maintains the position of thenerve within the electrode trough up until the point at which connectivetissue growth has secured the nerve and electrode 620 interface.

FIG. 6G shows a flat-bottomed variant 625 of an open trough electrode.While the contemporary textbook view of the shape of peripheral nervesis that of rounded structures, they may in fact also assume oval orflattened shapes depending upon their internal structure and where theylie in respect to other tissue structures such as muscles, bones, andfascial planes. One of the internal structure determinants ofcross-sectional shape may be the absence or presence of fascicularorganization. The design of a flat-bottomed open trough electrode 625advantageously allows a flattened nerve to lie against a series ofcontacts on a flattened surface, thereby also allowing a lower profilebetween the tissue structures where the peripheral nerve occurs.

In some embodiments of the present invention, an implantableneurostimulator system includes at least one flat-bottomed open troughelectrode 625. In some embodiments, an absorbable suture material 627 isplaced between the flaps 626 of the electrode 625 to prevent the nervefrom moving out of the trough during the connective tissue growth periodafter initial implantation. In some embodiments, the suture material 627has a finite lifetime before dissolving. This limits the potential forlong-term damage that might result from a permanent compressive orretentive mechanism such as a hard flap or fixed diameter cuff. In someembodiments, the flat-bottomed open trough electrode 625 provides ameans of selective activation that only temporarily constrains the nervewithin the electrode, and presents a lower profile for the same crosssectional nerve area than a comparable rounded trough electrode.

B. Electrode Configurations

The fully encircling cuff, helical cuff, and open trough electrodes canbe configured as monopolar, bipolar or multipolar electrodes. Forexample, electrodes may be composed of at least one pair ofplatinum/iridium cathode and anode contacts arranged in a helicalpattern on a substrate of heat shaped, biocompatible polystyrene stripmaterial. The contact pairs are oriented transversely to the HGN todrive stimulus into internal nerve fibers. In another embodiment theelectrode design is a helix. In another embodiment, the electrode designis a cuff with fingers, and in another embodiment, the electrode designis an electrode that penetrates the nerve itself. FIGS. 7A-9B showselected exemplary embodiments of these electrode configurations. Thenumber and arrangement of the contacts shown in each of these figuresare exemplary only, and not limited to what is shown.

1. Monopole Electrode Configuration

FIGS. 7A and 7B show exemplary embodiments of monopole electrodeconfigurations. Monopolar stimulation typically results in loweredstimulation thresholds since there is no shunting of current betweencontacts before it is free to enter the nerve bundle. FIG. 7A shows anexemplary embodiment of a monopolar, single cathodal contact, IPG casereturn electrode 700. In the configuration shown, a stimulationelectrode contact 702 acts as the excitatory cathodic contact, with theIPG case 701 providing the complementary current return path. FIG. 7Bshows an exemplary embodiment of a monopolar, single cathodal contact,indifferent array return electrode 710. In the embodiment shown in FIG.7B, a stimulation electrode contact 711 acts as the excitatory cathodiccontact, with another array of contacts (an indifferent array) 713furnishing the complementary current return. The indifferent array 713has one or more contacts, with the indifferent array contacts 713typically having a larger surface area than the excitatory contact.

In monopolar or bipolar stimulation, the waveform is often asymmetricalbiphasic, since it is sometimes undesirable to have a final excitatoryphase of cathodic stimulation on the case electrode. Those skilled inthe art of electrical stimulation understand that symmetrical biphasicpulses may result in excitatory cathodic phases of stimulation at eachof the necessary contacts of a stimulation electrode. By utilizingasymmetrical waveforms the first cathodic phase is of an amplitude andphase duration adequate to achieve excitation of the nerve, but thelater anodic phase is both longer and of lower amplitude, which at thereturn or second electrode contact, results in a cathodic phase which isnot of sufficient amplitude to cause nerve excitation. The commonpractice of using a large indifferent or case electrode at a locationaway from the nerve electrode acts to reduce current density at theindifferent electrode at a site away from the nerve, which alsominimizes the likelihood of excitation at that electrode.

2. Bipolar Electrode Configuration

FIG. 8 shows an exemplary embodiment of a bipolar electrodeconfiguration 800. Bipolar electrode configurations 800 have twocontacts with approximately the same geometric surface area stimulatingas a pair. One electrode is the excitatory contact 801 and the otherelectrode is the return (indifferent) contact 803. The charge deliveredand recovered by both contacts is approximately equal. Therefore, thereturn (indifferent) contact 803 can cause nerve 802 excitation duringthe last phase of the waveform if the waveform is symmetrical, and cancause anodic phase excitation depending upon the orientation and otherfeatures of the nerve 802 within the vicinity of the second contact 803.If the waveform utilized in bipolar stimulation is symmetrical then itis likely that excitation will occur at each electrode contact. If thewaveform is asymmetrical, it is likely that excitation will only occurat the primary cathodic contact 801.

3. Multipolar Electrode Configuration

Multipolar configurations allocate three or more contacts to stimulateas an array. FIGS. 9A and 9B show exemplary embodiments of multipolarelectrode configurations. FIG. 9A shows an exemplary embodiment of amultipolar, two cathodal contact, IPG case return multipolar electrodearray 900. The cathodal contacts 902, 905 typically function as theexcitatory contacts. Although only two cathodal contacts 902, 905 areshown, each with their own source, additional cathodal contacts (witheither independent or shared sources), may be used without departingfrom the scope of the invention. In the embodiment shown, the IPG case901 provides the complementary current return. This embodiment isexemplary only, and not limited to what is shown.

FIG. 9B shows an exemplary embodiment of a multipolar, two cathodalcontact, indifferent contact return multipolar electrode array 910. Thecathodal contacts 913, 914 typically function as the excitatorycontacts. Although only two cathodal contacts 913, 914 are shown, eachwith their own source, additional cathodal contacts (with eitherindependent or shared sources), may be used without departing from thescope of the invention. In the embodiment shown, another array ofcontacts (the indifferent array) 911 provides the complementary currentreturn. This embodiment is exemplary only, and not limited to what isshown.

In multipolar configurations, current fields may be manipulated indifferent or multiple directions, thereby changing neural recruitmentpatterns, and may do so without adversely spilling over or recruitingundesired neural populations. This mode of operation is best served bycurrent sources for each electrode contact that can be activatedconcurrently, i.e., by a single timing generator. Alternatively,multiple timing generators may be used with multiple contacts to recruitdifferent populations of neurons offset in time that result inapproximately simultaneous activation of the motor units with which theyassociate. This occurs because of the relatively long time constant ofmuscle activation with respect to motor nerve recruitment but is not tobe confused with concurrent stimulation as described previously, whichcan result in neural recruitment patterns unsupportable by singlecurrent source multiplexed stimulation alone or summated in time formotor unit recruitment.

C. Electrode Waveforms

These electrodes generate excitatory contact waveforms and complementarycontact waveforms to stimulate targeted nerves or nerve fibers.Stimulation frequency is adjustable from approximately 1 Hertz (Hz) toapproximately 100 Hz or higher. Typical frequencies for producing atetanic contraction range from approximately 15 Hz to approximately 60Hz. Lowering the frequency to the lowest required for a smooth, tetanic,and comfortable contraction reduces device power consumption and reducesmuscle fatigue elicited by electrical stimulation. These stimulationpatterns are exemplary only, and not limited to what is described. Whileonly excitatory contact waveforms and complementary contact waveformsare explained below, other stimulation waveforms of other stimulationfrequencies may be used without departing from the scope of theinvention.

1. Excitatory Contact Waveforms

Excitatory electrode contact waveforms may be symmetrical orasymmetrical biphasic, cathodic phase first, followed by a shortinterphase interval, followed by an anodic (charge recovery) phase. Thefirst cathodic phase ranges from approximately 10 to approximately 1000microseconds long. The interphase interval can be as short asapproximately 10 microseconds and as long as approximately 250microseconds, and is set to 50 microseconds by default. The interphaseinterval is set to be long enough to allow the first cathodic phase toachieve its full recruitment function before the charge recovery phaseoccurs. Shortening the interphase interval to less than the recruitmenttime would diminish the effect of the cathodic phase and waste a portionof the energy supplied during recruitment. The anodic phase duration andamplitude are approximately identical to the cathodic phase for asymmetrical biphasic waveform, and the anodic phase of an asymmetricalwaveform is approximately six times the duration of the cathodic phasein certain embodiments, with a concomitant phase amplitude approximatelyone-sixth the amplitude of the cathodic phase.

In the symmetrical and asymmetrical waveforms, the charge deliveredduring the cathodic phase is approximately equal to the charge recoveredin the anodic phase. In certain embodiments, ceramic coupling capacitorsin series with the output circuitry to each electrode contact helpmaintain the charge balance and prevent the passage of direct current,known to be harmful to tissue and which may increase the likelihood offailure in feedthroughs of the electronics enclosure. The couplingcapacitors must be large enough to pass current phases withoutsignificant droop.

2. Complementary Contact Waveforms

Complementary electrode contact waveforms have the opposite polarity asexcitatory electrode contact waveforms, but similar amplitude and phaseduration characteristics. If the waveform is symmetrical biphasic, thethird phase of the waveform at the complementary contact is cathodic,and could excite nerves in its vicinity. If the waveform isasymmetrical, the third phase of the waveform would be cathodic as well,but its amplitude would be roughly one sixth of the excitatory contactamplitude, and would be unlikely to excite any nerves.

D. Electrode Power

In the embodiments discussed above, independent current sources powereach electrode contact. Each contact is driven by its own currentgenerator, which sources or sinks up to approximately 12.7 mA in 0.1 mAsteps. The compliance voltage is the voltage that the current generatorutilizes for constant current generation for each current source, and inthe exemplary embodiment shown is approximately 18 volts. In otherembodiments, compliance voltage ranges from approximately 15 toapproximately 20 volts. The expected bipolar electrode to tissueimpedance is approximately 500 to 1500 ohms. Assuming anelectrode-to-tissue impedance of 1000 ohms, it would take roughly 1 voltof compliance voltage to drive 1 mA of current through the electrodecontact, and roughly 12.7 volts to drive 12.7 mA of current through theelectrode contact for the initial access voltage portion of the pulse,and higher voltages as the current is maintained through the couplingcapacitor. Since the outputs are capacitively coupled, the compliancevoltage should be greater than this initial access voltage to maintainthe current for the duration of the pulse phase. Compliance voltage ischosen based on factors such as maximum current desired, maximum phaseduration desired, coupling capacitor size, and expense of providing highvoltage power supplies to maintain constant current for the duration ofthe pulse phase.

Total current delivered to all contacts typically does not exceed thesteady state output of the IPG power supply. Current in this exemplaryembodiment is limited to approximately a 20 mA concurrent output.Overall current consumption depends on many factors, including, forexample, phase duration, phase amplitude, and pulse frequency. Takingthese factors into account, the total current output in the exemplaryembodiment is approximately 2 mA. The current and voltage levels inthese embodiments are exemplary only however. Other power levels may beused without departing from the scope of the invention.

III. IPG Nerve Stimulation

The embodiments described above allow for accurate, selective nervestimulation, including for example, the HGN. By accurately andselectively stimulating the HGN with multiple independent currentsources and site-specific multiple contact electrodes, often incombination with patient specific stimulus programming, only theportions of the HGN responsible for non-timing dependent activation arerecruited and activated, enabling accurate open-loop stimulation. Theseexemplary embodiments incorporate independent and concurrentstimulation, enabling optimal selective stimulation of only the desiredportions of the HGN.

This independent and concurrent stimulation produces the desired tonguemovement without needing to sense breathing related events to achievedesired results. Other embodiments of the IPG can include timedstimulation. Timed stimulation allows for triggered open loop or fullyclosed loop stimulation. Various examples of stimulation are discussedin U.S. Patent Application Nos. 60/978,519 and 61/017,614 filed on Oct.9, 2007 and Dec. 29, 2007 respectively, which are incorporated herein byreference. The sections below describe how nerves are recruited, andinclude examples of stimulation patterns generated with these exemplaryembodiments. These patterns are exemplary only, and not limited to thosediscussed below.

A. Nerve Structure, Activation, and Recruitment

One of the contributors to nerve activation threshold is nerve fiberdiameter. Due to the electrical cable properties of the nerve fibers,large diameter nerve fibers have a lower excitation threshold thansmaller diameter fibers, and are more easily excited by electricalstimulation. Thus, nerve fibers are more likely to be recruited by anelectrical stimulation pulse if they are closer to the activatingelectrode, and/or have a larger diameter than other fibers.

B. Force Vectoring and Field Steering

Multiple contact electrodes may be used in conjunction with multiplexedstimulator systems to co-activate multiple muscle groups to achieve adesired muscle response. In activating the muscles of the tongue, hand,or forearm, for instance, several contacts may be sequentially energizedto deliver interlaced pulses to first one contact and then another, toactivate two or more muscle groups that when added result in a forcevector in the desired direction. This is force vectoring.

FIGS. 10A and 10B show an example of a multiplexed system using forcevectoring. Even using force vectoring, multiplexed or single-sourceelectrodes have limitations in the stimulation patterns they coulddeliver. For example, with a single cathodic phase current from a singlecontact, the nerve fibers closest to the contact are the first to berecruited or activated (assuming uniform distribution of fiberdiameters, etc). As shown in FIG. 10A, even if the source weremultiplexed to multiple contacts however, the waveform generator 1000would connect to each contact 1005-1008 via a switching network1001-1004. FIG. 10B illustrates this with an example. As shown in FIG.10B, only a single waveform can be sent at any given time. First,channel 1 is enabled (i.e., switched on) and a waveform is generated forchannel 1 by a single waveform source. When the channel 1 waveform iscomplete, channel 1 is disabled (i.e., switched off). Once channel 1 isdisabled, channel 2 is enabled, and a waveform is generated for channel2 using the same waveform source. Simultaneous transmission of multiplewaveforms is not possible with this design.

FIGS. 11A and 11B show exemplary embodiments of non-multiplexed waveformgenerators 1100. These embodiments are used for field steering. Fieldsteering solves the limitations of force vectoring. Field steering usesindependent current sources and multiple electrode contacts together todefine a volume of activated nerve fibers. Field steering uses multipleindependent current sources to generate highly selectivepatient-specific activating current volumes.

Field steering is more selective than simple force vectoring. Fieldsteering (also known as current steering) enables activation of aparticular region or volume of nerve fibers near two or more electrodecontacts by controlling the cathodic phase amplitude generated by eachof the contacts independently. For example, using two cathodic contacts1101 and 1102 with equal phase amplitudes (for example by connecting twocontacts to a single current source or by setting independent currentsources to the same amplitude), applying a stimulus to the contactsdefines a neural activation volume constrained to a region approximatelyequidistant between the two contacts. In this configuration, asub-threshold phase current on each of the contacts 1101 and 1102 couldbe delivered, which combine to form an overlapping current field withsupra-threshold current field. As previously discussed, with twoelectrodes of equal current the central volume between the electrodes isthe activated nerve region.

Field steering allows the ability to change the activation area bychanging the proportion of cathodic phase current from a 50-50 split(requiring independent multiple current sources), thereby shifting thecurrent volume from the midline to a region closer to the higher phasecurrent source electrode contact. In field steering, independent currentsources are connected to individual electrodes and energizedapproximately simultaneously to define a volume where nerve fibers willbe activated. In order to activate a selected pool of neurons locatedsomewhere between two contacts, a stimulator delivers coincidentstimulation pulses. They are delivered simultaneously rather thansequentially multiplexed. In the example shown in FIG. 11A,sub-threshold currents are delivered to each contact 1101-1104 so thatthe fields around the individual contacts are below the recruitmentthreshold. As shown in FIG. 11B, the currents need not be identical. Thepulse phase durations are approximately equal, but amplitudes may differbecause they are generated by independent current sources. The fieldscombine in the targeted nerve area to create pulses sufficient tostimulate the targeted nerve or nerves. Thus, nerve populations otherthan those lying directly under a stimulation electrode contact can bepreferentially and selectively activated to achieve a desired stimuluspattern. This is important because the desired region of activationmight not be positioned directly under a stimulation contact due to thesurgical approach or a lack of a priori understanding of nerve fiberorganization prior to the application of stimulation, but which allowsfor the later adjustment of this stimulation field to achieve thedesired result.

IV. Stimulation Triggering and Measurement

The apparatus, system, and methods described above may use open loopstimulation, triggered open loop stimulation, and closed loopstimulation, either separately or in combination, to controlstimulation. Closed loop can use sensors and signals to initiatestimulation and to regulate its output so that a desired output functionis obtained. Triggered open loop stimulation uses one or moremeasurements as triggers for initiating stimulation. These triggers maybe obtained using one or more internal sensors, external sensors, or acombination of both. Internal sensors can be included in the IPGimplant, while external sensors would transmit trigger information tothe IPG implant. The triggers can be transmitted to the IPG implantwirelessly (for example by RF, Bluetooth, or other wireless means knownto those skilled in the art), or by operatively connecting the externalsensor to the IPG implant.

Examples of triggers include, but are not limited to, snoring, airflow,actigraphy, hypoxia, tongue position, and tongue protrusion. In certainexemplary embodiments, snoring could be detected internally using avibration sensor in the IPG implant. In other embodiments, snoring couldbe detected internally using an acoustic sensor and sound processor. Instill other embodiments, snoring could be detected externally using, forexample, a nasal canula or a microphone placed in the ear. Airflow couldbe measured externally using a nasal canula or thermistor and used as atrigger or as a closed loop feedback signal. Actigraphy could bemeasured using, for example, an accelerometer, which could be locatedinternally or externally. Hypoxia could be measured internally using,for example, an infrared source and sensor in the IPG implant, orexternally using an earlobe-monitoring unit. Tongue position could alsobe used as a trigger using, for example, a proximity sensor, whiletongue protrusion could be used as a trigger using, for example, anaccelerometer. These triggers could be used at any time, includinginitial placement, programming, and/or IPG implant calibration.

V. Auto Titration

Any combination of parameters measured in open loop, triggered openloop, and closed loop stimulation can be used to program and/or controlstimulation. In certain embodiments, one or more measured parameters areused to alter stimulation programming automatically in real time inresponse to changes in user condition. This is auto titration.

Auto titration may be performed during initial implantation andprogramming, during normal IPG system operation, or both. For example,auto titration may be used to optimize IPG implant settings while thepatient is in a medical facility, such as a clinic or hospital, aphysician's office, a sleep laboratory, or while the patient is at home(home titration). Small changes to stimulation parameters andconfigurations are made while observing their effect on one or moreindicators such as airway diameter, airway resistance, airflow, snoring,or other generally accepted measurements used to evaluate obstructivesleep apnea.

Clinician input and other related events may also be entered toassociate these indicators with patient sleep phases, including EEG andmanual selection/confirmation of phase identification. Since sleepphases greatly affect the range of sleep disordered breathing (SDB)measurements, and since there may be significant delays in effectsresulting from changes in stimulation parameter and configurationchanges, computers may be used to assist with data analysis andconfirmation of clinician assessments in a semi-automated system. Incertain titration embodiments, the titration system has an automatedprogramming capability (i.e., an auto titration system). For example,certain exemplary titration embodiments use predetermined algorithms toalter stimulus in response to detection of apnea indicators. In certainexemplary embodiments, the auto titration system is portable.

Auto titration may also be used during normal IPG implant operation. Forexample, in certain embodiments a sensor, which may be in the IPGimplant or the external patient controller, monitors a respirationindicator like air flow, for example. When the indicator drops, forexample if flow decreases by 10% below average unobstructed sleepingpatient flow, or snoring is detected, the IPG implant or externalcontroller slowly increases stimulus to cause an improvement in themonitored indicator (e.g., an increase in airflow and/or a decrease insnoring). If the sensor is connected to the IPG implant, the IPG implantchanges stimulation parameters. If the sensor is connected to anexternal controller, the controller changes simulation parameters, or ittriggers a preprogrammed increase in the IPG implant. The indicators areexemplary only. Other indicators known to those skilled in the art maybe used without departing from the scope of the invention.

It will be apparent to those skilled in the art that variousmodifications and variations can be made in the Apparatus, System, andMethod for Selective Stimulation without departing form the spirit orscope of the invention. Thus, it is intended that the present inventioncover the modifications and variations of this invention provided theycome within the scope of the appended claims and their equivalents.

1. An implantable neurostimulator system, comprising: a hollowcylindrical electronics enclosure having a top, a bottom, and a side; acoil extending from a first part of the electronics enclosure; and atleast one electrode operatively connected to the electronics enclosure.2. The implantable neurostimulator of claim 1, wherein the coil is atleast partially integral with the molded body.
 3. The implantableneurostimulator of claim 1, further comprising a magnet.
 4. (canceled)5. The implantable neurostimulator of claim 1, wherein the electronicsenclosure contains a microcontroller and custom ASIC. 6-9. (canceled)10. The implantable neurostimulator of claim 1, further comprising atleast one power source.
 11. The implantable neurostimulator of claim 10,wherein the at least one power source is an RF device.
 12. Theimplantable neurostimulator of claim 10, wherein the at least one powersource is an ultracapacitor. 13-14. (canceled)
 15. The implantableneurostimulator of claim 1, wherein the neurostimulator receives powerand telemetry commands from at least one external source.
 16. Animplantable neurostimulator system, comprising: a symmetricalchevron-shaped molded body having an apex, a first and a second side,and a base; a coil at the apex of the molded body; an electronicsenclosure at least partially integral with the molded body; and at leastone electrode operatively connected to the electronics enclosure. 17.The implantable neurostimulator of claim 15, wherein the implant has atleast one hole along at least one of the first and second sides of themolded body.
 18. A neurostimulator electrode, comprising: a cuff havinga first and a second surface; at least one contact on one of the firstand second surfaces; and means for delivering a stimulus to the at leastone contact.
 19. (canceled)
 20. The neurostimulator electrode of claim18, wherein the cuff is expandable. 21-22. (canceled)
 23. Theneurostimulator electrode of claim 18, wherein the cuff is helicallyshaped.
 24. The neurostimulator electrode of claim 18, wherein the cuffis at least partially circular.
 25. (canceled)
 26. The neurostimulatorelectrode of claim 24, wherein the cuff is self-sizing.
 27. Theneurostimulator electrode of claim 18, wherein the cuff overlaps atleast a portion of itself to form an empty space defined by the secondcuff surface. 28-31. (canceled)
 32. The neurostimulator electrode ofclaim 18, further comprising at least two contacts.
 33. (canceled) 34.The neurostimulator electrode of claim 32, wherein each contactindividually connects to a stimulation source.
 35. The neurostimulatorelectrode of claim 18, further comprising a first and second contactarray.
 36. The neurostimulator electrode of claim 35, wherein thesurface area of the second contact array is larger than the surface areaof the first contact array. 37-38. (canceled)
 39. A method ofneurostimulation, comprising the steps of: at least partially encirclinga nerve with a cuff having a first and a second surface, the cuff havingat least one contact on one of the first and second surfaces; connectingat least one stimulus generator to the at least one contact; anddelivering a stimulus to the at least one contact. 40-47. (canceled)